US7065399B2 - Muscle fatigue level measuring device - Google Patents
Muscle fatigue level measuring device Download PDFInfo
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- US7065399B2 US7065399B2 US10/697,100 US69710003A US7065399B2 US 7065399 B2 US7065399 B2 US 7065399B2 US 69710003 A US69710003 A US 69710003A US 7065399 B2 US7065399 B2 US 7065399B2
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- effective length
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/45—For evaluating or diagnosing the musculoskeletal system or teeth
- A61B5/4519—Muscles
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/053—Measuring electrical impedance or conductance of a portion of the body
Definitions
- the present invention relates to a muscle fatigue level measuring device which estimates the level of fatigue of muscles present in a body part (i.e., muscle fatigue level) based on impedance in the body part.
- muscle fatigue evaluation devices place electrodes on a body part so as to measure a change in potential (myoelectric potential) caused by contraction of muscles present in the body part and evaluate (determine) muscle fatigue (muscular fatigue) (for example, refer to Patent Publications 1 and 2).
- the conventional muscle fatigue evaluation devices (muscular fatigue determination devices) have a problem that the electrodes must be placed at the same distance from each other every time the measurement is made because the magnitude of the measured myoelectric potential varies if the distance between the electrodes placed on the body part varies.
- an object of the present invention is to solve the above problem of the prior art and provide a muscle fatigue level measuring device which estimates a muscle fatigue level without being influenced by a distance between electrodes.
- a muscle fatigue level measuring device of the present invention comprises:
- the impedance component measuring means comprises:
- the alternating currents of multiple frequencies are an alternating current with a frequency of 50 kHz and an alternating current with a frequency of 6.25 kHz.
- the muscular tissue effective length measuring means comprises:
- the muscle fatigue level determination means computes the muscle fatigue level by dividing the extracellular fluid resistivity by the distribution membrane capacitance.
- the muscle fatigue level determination means further computes a more accurate muscle fatigue level by considering at least one of personal data including a body weight, a body height, age and sex in addition to the computed muscle fatigue level.
- the muscle fatigue level measuring device of the present invention comprises:
- the electrode sets are disposed at the positions on the second ranging portions which correspond to the part length via flexible, elastic members.
- FIG. 1 is a block diagram showing a functional constitution of a muscle fatigue level measuring device according to the present invention.
- FIG. 2 is a front view of the muscle fatigue level measuring device at the time of measurement.
- FIG. 3 is a plan view of the muscle fatigue level measuring device at the time of measurement.
- FIG. 4 is a bottom view of the muscle fatigue level measuring device at the time of measurement.
- FIG. 5 is a right side view of the muscle fatigue level measuring device at the time of measurement.
- FIG. 6 is a block diagram showing a structural constitution of the muscle fatigue level measuring device according to the present invention.
- FIG. 7 is a main flowchart showing the procedure for using the muscle fatigue level measuring device according to the present invention and the operation of the device.
- FIG. 8 is a subroutine flowchart showing steps for measuring impedance in a body part.
- FIG. 9 is a subroutine flowchart showing steps for determining a muscle fatigue level in a body part.
- FIG. 10 is a biologically equivalent model.
- Reference numeral 1 denotes a main body; 2 and 3 denote first ranging portions; 4 ( 4 a , 4 b ) and 5 ( 5 a , 5 b ) denote second ranging portions; 13 b , 14 b , 15 b , and 16 b denote current-carrying electrodes; 13 c , 14 c , 15 c , and 16 c denote measuring electrodes; 21 denotes impedance component measuring means; 22 denotes muscular tissue effective length measuring means; 23 denotes biologically equivalent model parameter computation means; 24 denotes muscle fatigue level determination means; and 100 denotes a body.
- FIG. 1 a functional block diagram shown in FIG. 1
- FIG. 2 a front view of the device at the time of measurement which is shown in FIG. 2
- FIG. 3 a plan view thereof which is shown in FIG. 3
- FIG. 4 a bottom view thereof which is shown in FIG. 4
- FIG. 5 a structural block diagram shown in FIG. 6
- FIG. 10 a biologically equivalent model shown in FIG. 10 .
- the outer shape of the muscle fatigue level measuring device of the present invention is roughly formed by a main body 1 , first ranging portions 2 and 3 , and second ranging portions 4 and 5 ( 4 a and 4 b , and 5 a and 5 b ).
- the main body 1 constitutes the base of the present device and has a cylindrical shape. It incorporates an electronic circuit board on which an electric power source 31 , an oscillator 32 , a V/I converter 33 , a current-carrying electrode selector 34 , a measuring electrode selector 35 , an amplifier 36 , a filter 37 , an A/D converter 38 , a storage unit 39 , a display unit 40 and a CPU 41 are mounted.
- the first ranging portions 2 and 3 serve as jaws for measuring a part width in a body part and each have a prismatic shape.
- the portions 2 and 3 are attached to the main body 1 such that they can slide freely along the direction of the cylinder axis of the main body 1 (or the direction of the part width in the body part) and extend in a direction perpendicular to the cylinder axis direction of the main body 1 (or the direction of the part width in the body part).
- first electrodes 21 a and 22 a are provided on the guide surface of the main body 1
- second electrodes 21 b and 22 b are provided on the guide surfaces of the first ranging portions 2 and 3 .
- These first electrodes 21 a and 22 a and second electrodes 21 b and 22 b form first encoders 21 and 22 .
- they detect relative displacement magnitudes between the main body 1 and the first ranging portions 2 and 3 and output the data to the CPU 41 .
- the second ranging portions 4 and 5 serve as jaws for measuring a part length in a body part and comprise a pair of prismatic members 4 a and 4 b and a pair of prismatic members 5 a and 5 b , respectively.
- the members 4 a and 5 a are attached to the members 4 b and 5 b such that the members 4 a and 5 a can slide freely inside the members 4 b and 5 b , respectively.
- the second ranging portions 4 and 5 are disposed at the front ends of the first ranging portions 2 and 3 such that the prismatic members 4 a and 5 a slide in a direction perpendicular to the cylinder axis direction of the main body 1 and the prism axis directions of the first ranging portions 2 and 3 (or the direction of the part length in the body part).
- third electrodes 23 a and 24 a are provided on the guide surfaces of the prismatic members 4 a and 5 a
- fourth electrodes 23 b (not shown) and 24 b are provided on the guide surfaces of the prismatic members 4 b and 5 b
- These third electrodes 23 a and 24 a and fourth electrodes 23 b and 24 b form second encoders 23 and 24 .
- they detect relative displacement magnitudes between the prismatic members 4 a and 5 a and the prismatic members 4 b and 5 b and output the data to the CPU 41 .
- the second ranging portion 4 has an adjustment screw 6
- the second ranging portion 5 has an adjustment screw 7 and various switches 8 .
- the adjustment screws 6 and 7 fit screw grooves formed in the prismatic members 4 b and 5 b and press the prismatic members 4 a and 5 a through the prismatic members 4 b and 5 b so as to fix the positions of the prismatic members 4 a and 5 a and the prismatic members 4 b and 5 b when the prismatic members 4 a and 5 a slide within the prismatic members 4 b and 5 b .
- the switches 8 comprise an ON/OFF switch 8 a which switches between supplying electric power to units in the electrical system and stopping supplying the electric power to the units, an UP switch 8 b which increases a numerical value displayed on the display unit 40 at the time of setting of various data such as personal data (e.g., a body weight, a body height, age and sex), a DOWN switch 8 c which decreases a numerical value displayed on the display unit 40 at the time of setting of various data such as personal data (e.g., a body weight, a body height, age and sex), and a SET switch 8 d which sets a numerical value selected by use of the UP switch 8 b or the DOWN switch 8 c.
- personal data e.g., a body weight, a body height, age and sex
- a DOWN switch 8 c which decreases a numerical value displayed on the display unit 40 at the time of setting of various data such as personal data (e.g., a body weight, a body height
- electrode sets are disposed via springs 9 , 10 , 11 and 12 such that they face inward in the cylinder axis direction of the main body 1 .
- the electrode sets comprise plates 13 a , 14 a , 15 a and 16 a , current-carrying electrodes 13 b , 14 b , 15 b and 16 b , and measuring electrodes 13 c , 14 c , 15 c and 16 c . These electrodes are placed on the corresponding plates.
- the oscillator 32 generates constant voltages of different frequencies (50 kHz and 6.25 kHz).
- the V/I converter 33 receives the constant voltages generated from the oscillator 32 , converts the constant voltages to constant currents and outputs the constant currents.
- the current-carrying electrode selector 34 receives the constant currents output from the V/I converter 33 and outputs the constant currents to the given current-carrying electrodes 13 b and 16 b or 14 b and 15 b . Further, the current-carrying electrodes 13 b , 14 b , 15 b and 16 b serve as communication ports for passing the constant currents supplied from the current-carrying electrode selector 34 through a body part.
- the oscillator 32 , the V/I converter 33 , the current-carrying electrode selector 34 and the current-carrying electrodes 13 b , 14 b , 15 b and 16 b constitute current supply means for supplying alternating currents of multiple frequencies (50 kHz and 6.25 kHz) through a body part.
- the measuring electrodes 13 c , 14 c , 15 c and 16 c serve as communication ports for detecting voltages caused by impedance in the body part when the currents are passed through the body part from the current-carrying electrodes 13 b , 14 b , 15 b and 16 b .
- the measuring electrode selector 35 receives the voltages from the given measuring electrodes 14 c and 15 c , 13 c and 16 c and outputs the voltages.
- the amplifier 36 receives the voltages caused by the impedance in the body part from the measuring electrode selector 35 and amplifies and outputs the voltages.
- the filter 37 receives the voltages from the amplifier 36 and allows only specific frequency components (50 kHz and 6.25 kHz) to pass therethrough.
- the A/D converter 38 converts the voltages having passed through the filter 37 from analog signals to digital signals and outputs the digital signals to the CPU 41 .
- These measuring electrodes 13 c , 14 c , 15 c and 16 c , the measuring electrode selector 35 , the amplifier 36 , the filter 37 and the A/D converter 38 constitute voltage measuring means for measuring voltages of alternating currents of multiple frequencies (50 kHz and 6.25 kHz) occurring in a body part.
- the storage unit 39 stores various setting data set by means of the SET switch 8 d , and the display unit 40 displays various setting data and various measurement data.
- the CPU 41 serves as impedance component computation means, part width computation means, part length computation means, muscular tissue effective length computation means, biologically equivalent model parameter computation means 23 , and muscle fatigue level determination means 24 .
- the CPU 41 also controls units in the electrical system and performs computations in a known manner.
- the impedance component computation means divides the voltages of alternating currents of multiple frequencies (50 kHz and 6.25 kHz) received from the A/D converter 38 by the currents passing through the body part from the current supply means so as to compute a resistance component and a reactance component in the body part for each frequency (i.e., 50 kHz and 6.25 kHz).
- the above current supply means, voltage measuring means and impedance component computation means constitute impedance component measuring means 21 for measuring a resistance component and a reactance component in a body part as impedance in the body part.
- the part width computation means computes a part width Mw based on outputs received from the first encoders 21 and 22
- the part length computation means computes a part length Ml based on outputs received from the second encoders 23 and 24 .
- the muscular tissue effective length computation means substitutes the part width Mw computed by the part width computation means and the part length Ml computed by the part length computation means into an expression 7 so as to compute a muscular tissue effective length Meff in the body part.
- Meff k ⁇ square root over (Ml 2 ⁇ Mw 2 ) ⁇ wherein k is a correction coefficient (e.g., 1 ⁇ 2 1/2 which is experimentally predetermined).
- the above main body 1 , first ranging portions 2 and 3 and part width computation means constitute part width measuring means for measuring a part width Mw in a body part. Further, the above second ranging portions 4 and 5 and part length computation means constitute part length measuring means for measuring a part length Ml in a body part. Further, the above part width measuring means, part length measuring means and muscular tissue effective length computation means constitute muscular tissue effective length measuring means 22 for measuring a muscular tissue effective length in a body part.
- the biologically equivalent model parameter computation means 23 substitutes the real part ⁇ r and imaginary part j ⁇ x of complex resistivity which have been computed for each frequency (50 kHz and 6.25 kHz), a measuring frequency f, an imaginary number j and a pi ⁇ into an expression 9 for each frequency, and three equations are established based on the expression for each frequency (50 kHz and 6.25 kHz) so as to compute extracellular fluid resistivity Re, intracellular fluid resistivity Ri and distribution membrane capacitance Cm.
- the muscle fatigue level determination means 24 divides the extracellular fluid resistivity Re which has been computed by the biologically equivalent model parameter computation means 23 by the distribution membrane capacitance Cm so as to compute (determine) a muscle fatigue level K. Then, the muscle fatigue level determination means substitutes the computed muscle fatigue level K and personal data (body weight W, body height H, age Ag and sex S) set by the SET switch 8 d into an expression 10 so as to compute (determine) a more accurate muscle fatigue level Kh.
- Kh K ⁇ f 1( W ) ⁇ f 2( H ) ⁇ f 3( Ag ) ⁇ f 4( S ) wherein functions f 1 , f 2 , f 3 and f 4 are functions derived in advance from data collected from a number of subjects.
- numeric values corresponding to personal data are selected by the UP switch 8 b or the DOWN switch 8 c .
- the set personal data are stored in the storage unit 39 (STEP S 2 ).
- the second encoders 23 and 24 detect relative displacement magnitudes between the prismatic members 4 a and 5 a and the prismatic members 4 b and 5 b .
- the CPU (part length computation means) 41 computes an average (part length Ml) of a distance between the electrode sets 13 and 14 and a distance between the electrode sets 15 and 16 of the second ranging portions based on the detected relative displacement magnitudes (STEP S 3 ).
- the electrodes 13 b , 13 c , 14 b , 14 c , 15 b , 15 c , 16 b and 16 c are brought into direct contact with a body part whose muscle fatigue level is desired to be determined by adjusting a distance between the first ranging portions 2 and 3 .
- the first encoders 21 and 22 detect relative displacement magnitudes between the main body 1 and the first ranging portions 2 and 3 .
- the CPU (part width computation means) 41 computes a distance (part width Mw) between the electrode sets 13 ( 14 ) and 15 ( 16 ) based on the detected relative displacement magnitudes (STEP S 4 ).
- the current-carrying electrode selector 34 selects the current-carrying electrodes 13 b and 16 b
- the measuring electrode selector 35 selects the measuring electrodes 14 c and 15 c (STEP S 23 ).
- the constant current output from the V/I converter 33 passes through the body part situated between the current-carrying electrodes 13 b and 16 , and at that time, the measuring electrodes 14 c and 15 c detect a voltage produced in the body part (STEP S 24 ).
- the amplifier 36 amplifies and outputs the detected voltage.
- the filter 37 allows only a frequency component corresponding to 50 kHz to pass therethrough.
- the A/D converter 38 converts the analog signal to a digital signal and outputs the digital signal.
- the CPU (impedance component computation means) 41 computes a resistance component and a reactance component in the body part by dividing the voltage of 50 kHz by the current passing through the body part from the current supply means (STEP S 25 ).
- values displayed on the screen of the display unit 40 are updated with values of the resistance and reactance values in the body part when the measurement is determined to be stable (STEP S 28 ), and the values of the resistance and reactance values in the body part when the measurement is determined to be stable are stored in the storage unit 39 (STEP S 29 ).
- the register increases the currently registered value S by 1 and registers the updated value S (STEP S 30 ) and determines whether the updated S is larger than 2 or not (STEP S 31 ).
- STEPS S 23 to S 30 are carried out again (NO in STEP S 31 ).
- the current-carrying electrode selector 34 selects the current-carrying electrodes 14 b and 15 b
- the measuring electrode selector 35 selects the measuring electrodes 13 c and 16 c , under the control of the CPU 41 .
- the subsequent step is carried out (YES in STEP S 31 ).
- a muscle fatigue level is computed (STEP S 6 ).
- the CPU (muscular tissue effective length computation means) 41 substitutes the part length Ml computed in STEP S 3 and the part width Mw computed in STEP S 4 into the expression 7 so as to compute a muscular tissue effective length Meff in the body part (STEP S 51 ).
- the CPU (biologically equivalent model parameter computation means 23 ) 41 substitutes the muscular tissue effective length Meff, the resistance component R and reactance component jX at the time of measurement at 50 kHz stored in the storage unit 39 , and a resistance component R and reactance component jX at the time of measurement at 6.25 kHz into the expression 8 so as to compute a real part ⁇ r and imaginary part j ⁇ x of complex resistivity at the time of measurement at 50 kHz and a real part ⁇ r and imaginary part j ⁇ x of complex resistivity at the time of measurement at 6.25 kHz (STEP S 52 ).
- the CPU (muscle fatigue level determination means 24 ) 41 divides the extracellular fluid resistivity Re by the distribution membrane capacitance Cm so as to compute (determine) a muscle fatigue level K (STEP S 54 ). Then, the CPU (muscle fatigue level determination means 24 ) 41 substitutes the muscle fatigue level K and the personal data (body weight, body height, age and sex) set in STEP S 2 into the expression 10 so as to compute (determine) a more accurate muscle fatigue level Kh, whereby the computation of the muscle fatigue level is completed (STEP S 55 ).
- the display unit 40 displays the muscle fatigue level K or more accurate muscle fatigue level Kh on the screen (STEP S 7 ).
- the power source 31 stops supplying electric power to the units in the electrical system, whereby a series of procedural steps of the present device are completed (STEP S 8 ).
- the muscle fatigue level measuring device of the present invention measures a resistance component and a reactance component in a body part as impedance in the body part by the impedance component measuring means 21 , measures a muscular tissue effective length in the body part by the muscular tissue effective length measuring means 22 , computes biologically equivalent model parameters including extracellular fluid resistivity and distribution membrane capacitance based on these resistance component, reactance component and muscular tissue effective length by biologically equivalent model parameter computation means 23 , and determines a muscle fatigue level based on the ratio of the extracellular fluid resistivity to the distribution membrane capacitance by the muscle fatigue level determination means 24 .
- the muscle fatigue level measuring device of the present invention can obtain a muscle fatigue level with high accuracy since it obtains the muscle fatigue level in consideration of the muscular tissue effective length in the body part which is a distance between the electrodes.
- data serving as a basis for computing the muscular tissue effective length in the body part can be obtained by the first ranging portions 2 and 3 for measuring a part width which are disposed on the main body 1 such that they can slide freely in a part width direction in a body part and the second ranging portions 4 and 5 for measuring a part length which are disposed on the first ranging portions 2 and 3 such that they can slide freely in a path length direction in the body part.
- the measurement can be made more easily and more accurately.
- springs were used between the electrode sets and the second ranging portions so as to have the electrodes contact with the body part in good condition.
- the present invention can also be practiced by using rubber or other flexible, elastic members in place of the springs.
- the muscle fatigue level measuring device of the present invention has the muscular tissue effective length measuring means by which the device can obtain a muscle fatigue level in consideration of muscular tissue effective length in a body part.
- the obtained muscle fatigue level is highly accurate.
- the muscle fatigue level measuring device of the present invention measures a part width and a part length by the main body, first ranging portions and second ranging portions constituted such that distances in a body part can be changed so as to obtain a muscular tissue effective length in the body part.
- the muscle fatigue level can be obtained more easily and more accurately.
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Abstract
Description
- impedance component measuring means,
- muscular tissue effective length measuring means,
- biologically equivalent model parameter computation means, and
- muscle fatigue level determination means,
wherein - the impedance component measuring means measures a resistance component and a reactance component in a body part as impedance in the body part,
- the muscular tissue effective length measuring means measures a muscular tissue effective length in the body part,
- the biologically equivalent model parameter computation means computes biologically equivalent model parameters including extracellular fluid resistivity and distribution membrane capacitance based on the resistance component and reactance component measured by the impedance component measuring means and the muscular tissue effective length measured by the muscular tissue effective length measuring means, and
- the muscle fatigue level determination means determines a muscle fatigue level based on the ratio between the extracellular fluid resistivity and distribution membrane capacitance computed by the biologically equivalent model parameter computation means.
- current supply means,
- voltage measuring means, and
- impedance component computation means,
wherein - the current supply means supplies alternating currents of multiple frequencies to a body part,
- the voltage measuring means measures voltages generated in the body part by supplying the alternating currents of multiple frequencies by the current supply means, and
- the impedance component computation means computes resistance components and reactance components in the body part by dividing the voltages measured by the voltage measuring means by the currents supplied from the current supply means.
- part length measuring means,
- part width measuring means, and
- muscular tissue effective length computation means,
wherein - the part length measuring means measures a part length in the body part,
- the part width measuring means measures a part width in the body part, and
- the muscular tissue effective length computation means computes the muscular tissue effective length in the body part based on the part length measured by the part length measuring means and the part width measured by the part width measuring means.
Meff=k√{square root over (Ml 2 ×Mw 2 )}
wherein Meff represents the muscular tissue effective length, Ml represents the part length, Mw represents the part width, and k represents a correction coefficient.
(R+jX)/Meff=ρr+jρx
wherein R represents the resistance component, jX represents the reactance component, Meff represents the muscular tissue effective length, and ρr and jρx represent a real part and imaginary part of complex resistivity, respectively,
1/(ρr+jρx)=1/Re+1/(Ri+j×2π×f×Cm)
wherein Re represents the extracellular fluid resistivity, Ri represents the intracellular fluid resistivity, Cm represents the distribution membrane capacitance, f represents a measuring frequency, j represents an imaginary number, and π represents a pi.
- a main body,
- first ranging portions,
- second ranging portions, and
- electrode sets,
wherein - the main body serves as a base,
- the first ranging portions are disposed on the main body such that they can slide freely in a part width direction in a body part so as to measure a part width,
- the second ranging portions are disposed on the first ranging portions such that they can slide freely in a part length direction in the body part so as to measure a part length, and
- the electrode sets comprise current-carrying electrodes and measuring electrodes which are disposed at positions on the second ranging portions which correspond to the part length,
- the impedance component measuring means includes the electrode sets and measures a resistance component and a reactance component in a body part which is in direct contact with the electrode sets as impedance in the body part, and
- the muscular tissue effective length measuring means computes a muscular tissue effective length in the body part based on the part width measured by the first ranging portions and the part length measured by the second ranging portions.
Meff=k √{square root over (Ml 2 ×Mw 2 )}
wherein k is a correction coefficient (e.g., ½1/2 which is experimentally predetermined).
(R+jX)/Meff=ρr+jρx
1/(ρr+jρx)=1/Re+1/(Ri+j×2π×f×Cm)
Kh=K×f1(W)×f2(H)×f3(Ag)×f4(S)
wherein functions f1, f2, f3 and f4 are functions derived in advance from data collected from a number of subjects.
Claims (16)
Meff=k√{square root over (Ml 2 ×Mw 2 )}
Meff=k√{square root over (Ml 2 ×Mw 2 )}
Meff=k√{square root over (Ml 2 ×Mw 2 )}
(R+jX)/Meff=ρr+jρx
1/(ρr+jρx)=1/Re+1/(Ri+j×2π×f×Cm)
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Citations (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4667513A (en) * | 1981-03-18 | 1987-05-26 | Konno Yoshio | Method and apparatus for detecting muscle fatigue |
US5335667A (en) * | 1992-11-20 | 1994-08-09 | University Of Utah Research Foundation | Method and apparatus for determining body composition using bioelectrical impedance |
JPH06304157A (en) | 1993-04-14 | 1994-11-01 | Mega Electron Oy | Method for judging resistance and sensibility of muscle to fatigue |
JP2000000232A (en) | 1998-06-15 | 2000-01-07 | Toyota Central Res & Dev Lab Inc | Muscular fatigue judgement device |
US6185451B1 (en) * | 1997-05-09 | 2001-02-06 | The University Of Queensland | Muscle function assessment apparatus and method |
EP1114610A1 (en) | 2000-01-05 | 2001-07-11 | Tanita Corporation | Apparatus for determining degree of fatigue of human body |
JP2002224072A (en) | 2001-02-02 | 2002-08-13 | Mazda Motor Corp | Muscular fatigue evaluating device, muscular fatigue evaluating method, computer program for executing this method and storage medium for storing this computer program |
US6468232B1 (en) * | 2000-07-13 | 2002-10-22 | The Regents Of The University Of Michigan | Method and apparatus for measuring properties of the pelvic floor muscles |
US6714814B2 (en) * | 2000-03-30 | 2004-03-30 | Tanita Corporation | Bioelectrical impedance measuring apparatus |
US20040082877A1 (en) * | 2002-10-22 | 2004-04-29 | Tanita Corporation | Muscle measuring device |
US20040167386A1 (en) * | 2003-02-26 | 2004-08-26 | Tanita Corporation | Animal health care system |
-
2002
- 2002-12-25 JP JP2002373574A patent/JP3960475B2/en not_active Expired - Fee Related
-
2003
- 2003-10-31 US US10/697,100 patent/US7065399B2/en active Active
- 2003-12-17 DE DE60316401T patent/DE60316401T2/en not_active Expired - Lifetime
- 2003-12-17 EP EP03029076A patent/EP1433420B1/en not_active Expired - Fee Related
Patent Citations (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4667513A (en) * | 1981-03-18 | 1987-05-26 | Konno Yoshio | Method and apparatus for detecting muscle fatigue |
US5335667A (en) * | 1992-11-20 | 1994-08-09 | University Of Utah Research Foundation | Method and apparatus for determining body composition using bioelectrical impedance |
JPH06304157A (en) | 1993-04-14 | 1994-11-01 | Mega Electron Oy | Method for judging resistance and sensibility of muscle to fatigue |
US6185451B1 (en) * | 1997-05-09 | 2001-02-06 | The University Of Queensland | Muscle function assessment apparatus and method |
JP2000000232A (en) | 1998-06-15 | 2000-01-07 | Toyota Central Res & Dev Lab Inc | Muscular fatigue judgement device |
EP1114610A1 (en) | 2000-01-05 | 2001-07-11 | Tanita Corporation | Apparatus for determining degree of fatigue of human body |
US6516222B2 (en) * | 2000-01-05 | 2003-02-04 | Tanita Corporation | Apparatus for determining degree of fatigue of human body |
US6714814B2 (en) * | 2000-03-30 | 2004-03-30 | Tanita Corporation | Bioelectrical impedance measuring apparatus |
US6468232B1 (en) * | 2000-07-13 | 2002-10-22 | The Regents Of The University Of Michigan | Method and apparatus for measuring properties of the pelvic floor muscles |
JP2002224072A (en) | 2001-02-02 | 2002-08-13 | Mazda Motor Corp | Muscular fatigue evaluating device, muscular fatigue evaluating method, computer program for executing this method and storage medium for storing this computer program |
US20040082877A1 (en) * | 2002-10-22 | 2004-04-29 | Tanita Corporation | Muscle measuring device |
US20040167386A1 (en) * | 2003-02-26 | 2004-08-26 | Tanita Corporation | Animal health care system |
Cited By (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20060032315A1 (en) * | 2002-08-16 | 2006-02-16 | Sami Saalastic | Method for monitoring accumulated body fatigue for determining recovery during exercise or activity |
US7192401B2 (en) * | 2002-08-16 | 2007-03-20 | Firstbeat Technologies Oy | Method for monitoring accumulated body fatigue for determining recovery during exercise or activity |
US11660013B2 (en) | 2005-07-01 | 2023-05-30 | Impedimed Limited | Monitoring system |
US11737678B2 (en) | 2005-07-01 | 2023-08-29 | Impedimed Limited | Monitoring system |
US9724012B2 (en) | 2005-10-11 | 2017-08-08 | Impedimed Limited | Hydration status monitoring |
US11612332B2 (en) | 2005-10-11 | 2023-03-28 | Impedimed Limited | Hydration status monitoring |
US10307074B2 (en) | 2007-04-20 | 2019-06-04 | Impedimed Limited | Monitoring system and probe |
US10070800B2 (en) | 2007-08-09 | 2018-09-11 | Impedimed Limited | Impedance measurement process |
US9615767B2 (en) | 2009-10-26 | 2017-04-11 | Impedimed Limited | Fluid level indicator determination |
US9585593B2 (en) | 2009-11-18 | 2017-03-07 | Chung Shing Fan | Signal distribution for patient-electrode measurements |
US8700121B2 (en) | 2011-12-14 | 2014-04-15 | Intersection Medical, Inc. | Devices for determining the relative spatial change in subsurface resistivities across frequencies in tissue |
US9149225B2 (en) | 2011-12-14 | 2015-10-06 | Intesection Medical, Inc. | Methods for determining the relative spatial change in subsurface resistivities across frequencies in tissue |
Also Published As
Publication number | Publication date |
---|---|
JP3960475B2 (en) | 2007-08-15 |
DE60316401T2 (en) | 2008-01-24 |
EP1433420A1 (en) | 2004-06-30 |
EP1433420B1 (en) | 2007-09-19 |
DE60316401D1 (en) | 2007-10-31 |
US20040092840A1 (en) | 2004-05-13 |
JP2004201877A (en) | 2004-07-22 |
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